Radiography apparatus with photocell drift compensating means

ABSTRACT

In an apparatus for examining a body by means of penetrating radiation a source is arranged to direct radiation through the body and a plurality of detectors are arranged to receive it thereafter. The source and detector are arranged to scan the body to obtain data for use in obtaining a distribution of absorption of the radiation for part of the body. For correction for differences in the relative sensitivities of the detectors they are arranged in pairs to examine radiation along substantially identical paths and for correction for drift each detector is caused to examine a substantially identical path at different times.

This invention relates to a method of and apparatus for examining a body by means of radiation such as X- or γ- radiation.

The method and apparatus according to the invention can be used to assist in the production of radiographs in any convenient form, such as a picture on a cathode ray tube or other image forming device, a photograph of such a picture, or a map of absorption coefficients such as may be produced by a digital computer and on which contours may subsequently be drawn.

In the method of, and apparatus for, examining a body described in U.S. Pat. No. 3,778,614radiation is directed through part of the body, from an external source, in the form of a pencil beam. A scanning movement is imposed on the beam so that it takes up in turn a large number of differing dispositions, and a detector is used to provide a measure of the absorption of the beam in each such disposition after the beam has passed through the body. The beam is caused to take up these various dispositions by arranging that the source and the detector are reciprocated in a plane and are orbited about an axis normal to the plane. The various dispositions thus lie in a plane through the body over which the distribution of absorption coefficients for the radiation used is derived by processing the beam absorption data provided by the detector. The processing is such that the finally displayed distribution of absorption is the result of a linear superposition process coupled with successive approximations.

The method and apparatus described in the aforesaid Patent has proved to be successful for producing cross-sectional representation of parts of the living body, such as the head.

In the United States Ser. No. 532,188 . . .filed 12.12.74 /(Hounsfield et al) and now U.S. Pat. No. 3,999,073, there is described an apparatus for carrying out the derivation of the absorption data signals in a relatively rapid manner. According to this Patent Application the derivation is achieved by directing a sectoral swath of X-rays emanating from a source, through the body in the plane to be examined and providing a series of detectors on the other side of the body to measure the radiation transmitted along a set of beam paths within the swath. The sectoral swath subtends an angle sufficient to include the whole region of interest in the plane of the body, so that a complete scan can be effected merely by orbiting the source and the detectors about the body. When such an arrangement is adopted it is important that the absorption data signals should not include differences due to differential variations in the sensitivites of the various detectors. It is, however, found in practice that such differential variations can occur to a significant degree even in the relatively short time required for scanning.

It is an object of the present invention to provide means for reducing such spurious differences.

According to one aspect of the present invention there is provided an apparatus for examining a body by means of penetrating radiation such as X- or γ- radiation including source means arranged to irradiate a region of the body, detector means, including a plurality of detectors, arranged to determine the intensity of the radiation after passage through the body, scanning means arranged to scan said source and detector means to irradiate the body from a plurality of directions so that there can be derived, from said determinations of intensity, a reconstruction of the distribution of absorption of the radiation within a part of the body, means being provided to compare the outputs of said detectors in pairs at predetermined times when the respective detectors of a pair receives radiation along substantially identical paths to determine the differences in the relative sensitivities of said detectors during the scanning movement. According to a further aspect of the present invention there is provided a method of examining a body by means of penetrating radiation such as X- or γ- radiation including the steps irradiating a region of the body, detecting the intensity of the radiation, after passage through the body, moving the source of the radiation and a plurality of detectors with respect to the body so as to irradiate the body from a plurality of directions, deriving from said intensity determinations of reconstruction of the distribution of absorption of the radiation within a part of the body and comparing the outputs of said detectors in pairs at predetermined times in the course of the scanning movement to determine the extent of differences in the sensitivites of the detectors.

In order that the invention may be clearly understood and readily carried into effect, the same will now be more fully described with reference to the accompanying drawings in which:

FIG. 1 shows the general layout in side elevation of an apparatus in accordance with the invention;

FIG. 2 shows details of part of FIG. 1, together with a diagrammatic layout of the circuit concerned with processing of the absorption data;

FIGS. 3(a), 3(b), 3(c), 3(d), 3(e) and 3(f) are explanatory diagrams relating to means according to the invention whereby data is corrected for detector errors, and

FIG. 4 is a diagram illustrating the operation carried out by a digital computer included in the circuit of FIG. 2.

In FIG. 1 the patient 1 is shown lying on supporting means formed in two parts 2 and 3 and his body is subject to examination by X-radiation indicated in broken line at 4. This radiation is generated by a source 5 and forms a fan shaped spread in a plane lying at right angles to the plane of the figure. It will be appreciated that the patient supporting means has to be sufficiently long to allow any desired section of the patient's body to be located in the plane of the X-radiation.

In the region of the exploring radiation, the body of the patient is surrounded by a liquid medium, which may be water and which has an absorption coefficient for the radiation closely similar to that of body tissue. The liquid is shown in the figure at 6 and contained within an envelope, or bag 7. The envelope 7 is positioned within a ring like structure 8 which may be of metal such as duralumin. The ring member 8 is held by retaining means not shown in the figure. Supporting means 2 is mounted on an upright 9A of the main frame 9 of the apparatus whilst the part 3 is supported at its end remote from the ring member 8 by a bearing 10, carried by an axle member 11, which member has an axis about which orbiting motion of the X-ray source 5 takes place. Around the body of the patient, when he is located in position in the apparatus, there is disposed a surround or frame 13 which is cylindrical along its length, having a longitudinal axis which is the axis of the axle member 11. At its end adjacent this latter member, it is closed and supported by a bearing 14 which in turn is supported by the member 11. At its other end it is open to allow for positioning of the patient within it, and at this end it is supported on rollers 15 which have suitable fixed bearings. These rollers are such that the surround member 13 is free to rotate on its axis which, as has been indicated, is the axis about which the orbiting motion of the X-ray source 5 takes place. The source 5 is carried on the surround member 13 by means of a support 16. Directly opposite the source 5 there is carried on the surround member 13, by means of a support 17, a detector system 18 so as to provide radiation absorption data from the body of the patient in the plane of the radiation from the source 5. The detector system 18 extends over the whole spread of the fan of radiation from source 5. The spread of the fan is indicated diagrammatically in FIG. 2 as is the extent of the detector means 18. The supports for the detector system 18 allow limited angular movement of the system relative to the surround member 13, as will be described.

The axle member 11 is carried by a support 19 and adjacent the support 19 and surrounding the axle member 11 is a bobbin 20. This last element is fixed to the support 19 and wound round it are cables 21 and 22 respectively carrying absorption data from the detector means 18 to the processing unit and supplying power for the X-ray source 5. The cables 21 and 22 also supply electric current for electromagnets used for producing the aforesaid angular movements of the detector system 18. With the orbiting motion of the source and detector means the cables wind on or off the bobbin 20. They are fed to the bobbin via guides 23 and 24 respectively which are carried by the surround member 13. In this example of the invention, member 13 makes three revolutions for each examination cycle which is completed in a few seconds and the cables wrap or unwrap in relation to the bobbin 20 correspondingly, they are returned at the end of the examination. At the bobbin the cables are secured and thence pass to their respective connecting units, namely the data processing unit mentioned, and a power supply unit.

As indicated in FIG. 2, the detector means comprises a series of individual detectors 18₁. . .18_(k). . .18_(n), each arranged to detect the radiation transmitted along a narrow finger-like beam path 29₁. . .29_(n+1), indicated in the sectoral swath which is limited within the bounds 29 by suitably collimating the sources of radiation 5.

Each detector 18₁. . .18_(n) comprises in known manner a crystal which scintilates when a quantum of X-radiation or other high energy is incident upon it, and a photo-multiplier for converting the light scintillation to an electrical current impulse, such impulses forming the output signals of the individual detectors. Other forms of detector may however be used. Each scintillator is provided with a suitable collimator so that radiation is substantially prevented from reaching it other than from the respective beam path. The construction of the apparatus shown in FIG. 1 is only illustrated in outline and briefly described, since it may be generally similar in construction to that described in the United States Serial No. 532,188 filed 12.12.74 (Hounsfield et al). and now U.S. Pat. No. 3,999,073.

The orbiting movement of the surround member 13 and with it the source 5 and the detector system 18 is effected by an electric motor 30, mounted on the main frame 9 which drives the surround member 13 via gear wheels 31 and 32, the latter of which is fixed to the surround member 13. The motor also drives a switching mechanism 33 which operates as will be explained on the current supply for the electromagnets which produce angular movements of the detector system 18. The switching mechanism 33 also controls other supplies. FIG. 2 illustrates the electromagnet arrangement for the detector system. It comprises two coils 35 and 36 which operate an armature 37 attached to the detector system 18. The coils are connected in series with current supplied to a reversing switch 38 included in the switch mechanism 33. As shown, the detector system 18, which is a unitary structure is supported in guides 39 and attached to the surround member 13, the guide allowing a limited, but precise angular movement of the system 18. When the current supplied to the coils 35 and 36 has one sense, the system 18 is held in one of its limit positions on the guides 39, and when the current is reversed the system 18 is moved to the other limit position and held in that position. The switch mechansim 33 is arranged to operate the switch 38 after the first and again after the second of the three rotations of the surround member 13 which comprise the examination cycle of the apparatus. The movement of the detector system is very small, being only the angular separation between adjacent detectors 18₁. . .18_(n).

The effect of the operation of the reversing switch 38 is to cause the detectors 18₁. . .18_(n) to detect the radiation received along the beam paths 29₂. . . 29_(n+1) during the first and third revolution of an examination cycle and to detect radiation received along the beam paths 29₁. . .29_(n) during the second revolution of the examination cycle.

Referring further to FIG. 2 the output signals from the detector system 18 as they are produced in the course of the orbital motion of the apparatus are fed to respective amplifiers 231. The various output currents from the amplifiers are respectively integrated by Miller integrator circuits 232, over successive short intervals of time and the outputs of these circuits are respectively converted from analogue to digital form by converters 233 and fed to the digital computer 234, the operation of which maybe explained in connection with FIG. 4. If desired the gains of the amplifiers 231 may be commonly controlled to compensate for any variations that may occur in the emission intensity of the X-ray source.

The outputs of the digital computer are corrected beam data signals, each one representing the transmittance of radiation along one of the beam paths 29₁. . . 29_(k). . .29_(n) during an interval of time which is sufficiently short for it to be regarded as the transmittance along the stationary beam path at a particular angular position, notwithstanding the orbiting movement of the source 5 and the detector means 18. The beam path data signals are applied to beam data store 239 and thence via an address selector 251 to image reconstruction circuit 252 which may in fact utilise the digital computer 234. The image reconstruction will not be described here. It may be carried out in a variety of different ways but that described in the complete specification of U.S. Pat. No. 3,924,129 is preferred. It is sufficient for the purposes of the present invention to indicate that the address selector 251 withdraws data from storage in 239 in sets corresponding to output signals derived from parallel sets of beam paths, each set being processed in the circuit 252. It will be apparent from FIG. 2, that at any particular point in time (that is at any particular angular position of the sectoral swath 29) the beam paths 29₁. . .29_(k). . . are not parallel. However, the intervals of integration of the integrators 232 are so related to the orbiting movement of the source 5 and the detectors 18 that beam path data signals, derived from successive detectors 18₁. . .18_(n), during successive intervals of integration, represents the transmittance along parallel sets of beam paths. From a knowledge of the order of storage in store 239, sets of output signals corresponding to sets of parallel beam paths can be selected without difficulty. This mode of operation forms the subject matter of the United States Serial No. 544,799 filed Jan. 28, 1975 (Hounsfield) and based on a British patent application filed on the day of filing of the British application on which this U.S. specification is based. When the image reconstruction operations are complete, the image is displayed by a display system 134, for example a cathode ray tube or printer, or in addition or as an alternative, may be transferred to magnetic tape storage.

The gains of the amplifiers 231 are adjusted to compensate for differences in the sensitivites of the radiation detectors. This compensation is particularly important when high accuracy in image reconstruction is aimed at, for example accuracy such as one part in one thousand. Sensitivity differences tend to appear in the reconstruction as a fine ring-like pattern. However, it is found in practice that pre-set adjustment in amplifier gains is insufficient to compensate for differences in sensitivities. The invention is concerned with effective compensation for differences which may exist or arise during each actual examination.

It is possible to regard errors in the sensitivities of the detectors 18 as having two components, one dependent on the position of the detector (that is a difference in the sensitivity of the detector from a neighbouring detector) and the other dependent upon time (that is drift on the sensitivity of any one detector during the time occupied by an examination cycle). FIGS. 3(a) to 3(f) illustrate how these two components of error can be calculated approximately for each detector and used to correct the output data signals used in the image reconstruction. In each figure the area within which the body under examination must be located is shown by 13'. The figures indicate the beam paths along which radiation impinges on two detectors 18_(k) and 18_(k+1) at different times during the three revolutions of an examination cycle. FIG. 3(d) represents approximately the mid point of the second revolution at a time when, by virtue of the displacement of the detector system 18 affected by the electromagnets 35 and 36, the detectors k and k+1 are displaced, compared with their position at other times. The displacement is equivalent to displacing the orbital axis from 0 to 0'. One revolution is regarded as comprising 361, namely 0° to 360° inclusive, 1° of orbital movement occurring in each interval of integration of the integrators 232. The interval may however be smaller. The time occupied in each revolution of orbital motion is denoted by T and for mathematical convenience the time represented by FIG. 3(d) is taken as time t=o. The times represented by the other FIGS. 3(a), 3(b), 3(c), 3(e) and 3(f) are indicated alongside the respective figures. The absorption data derived during the first and third revolutions is used for image reconstruction following techniques already described.

In each part of FIG. 3, it is assumed that the source of the exploring radiation, although not shown, lies in the plane of the figure vertically above the orbital axis O. In FIG. 3(a) the path p denotes a particular radiation track through the material of the body, radiation from the source traversing this track falling upon the kth detector 18k of the detector system 18. Detector k+1 is the next adjacent detector and radiation falling upon this detector traverses the path q through the material of the body. In FIG. 3(c) an identical situation is shown, with the completion of one revolution of the scanning, but now on account of drifting of the sensitivites of the detectors the absorption data derived from the two detectors may be different.

In FIG. 3(b) the positions of the two detectors are shown after just one half revolution of the orbital scan, and p' and q' designate radiation tracks through the material of the body that impinge upon the two detectors k and k+1 in the position they now occupy. The tracks lie in antisymmetrical relation to the tracks p and q.

The tracks p' and q' are also shown in FIG. 3(d) but now with the shift of the detector system it is radiation traversing track p' that falls upon detector k+, 1 rather than radiation traversing track q'. This interchange of the two detectors in relation to the path p' enables the sensitivities of the two detectors to be compared, and the manner of this comparison will become clear, though as will be evident it is necessary to take into account the extent of the drift of detector sensitivity in the interval between the time t= -T of FIG. 3(b) and the time t=o of FIG. 3(d). FIGS. 3(e) and 3(f) relate to the beginning and end of the third revolution of the examination cycle; these figures are similar to FIGS. 3(a) and 3(c) but the paths of the radiation incident on the detectors k and k+1 are denoted as r and s respectively to allow for the slight difference in the starting angle of the third revolution compared with the first revolution.

In order to understand the correction process in more detail let S_(k) (t) represent the signal deriving from the kth detector at arbitary time t during the scanning operation. This signal will be proportional to the measure of absorption f(t) suffered by the exploring radiation along the path incident upon the detector at time t, and will also be proportional to the drift, D_(k) (t), in the sensitivity of the detector at time t. Thus it is possible to write

    S.sub.k (t) = A.sub.k D.sub.k (t)f(t).

A similar statement is true of the k+1thdetector. A_(k) may be termed the sensitivity constant of detector k. The output of detector k in FIG. 3(b) and that of detector k+1 in FIG. 3(d) are then

    S.sub.k (-T) = A.sub.k D.sub.k (-T)f.sub.O

    S.sub.k+1 (O) = A.sub.k+1 D.sub.k+1 (O)f.sub.O,

in which f_(O) is the measure of the absorption along path p' in FIG. 3(b) and equally so along path p' in FIG. 3(d). To simplify matters the drift factor for a detector may be taken as unity for time t=O, and it follows then that ##EQU1## The ratio ##EQU2## can then be determined, and can furthermore be determined for any pair of detectors, if the magnitude of the drift as represented by D_(k) (-T) can be determined. Therefore the relative sensitivities of the various detectors can be approximately compensated, providing that λ and D(t) can be determined in each case.

To obtain the information needed to evaluate D(t), consider first of all the situations relating to FIGS. 3(a) and 3(c). For these situations respectively ##EQU3## in which f₁ is the absorption measure along the path p. Again considering the respective situations of FIGS. 3(e) and 3(f) ##EQU4## of which f₂ is the absorption measure along the path p. From the first of the two pairs of equations it follows that ##EQU5## and from the second ##EQU6##

These results may be represented more compactly if Δ_(k1) is used to signify the first order slope of a function associated with the k th detector over the span ##EQU7## and Δ_(k2) likewise over the span ##EQU8## so that the results can be expressed respectively,

    Δk.sub.1 log S.sub.k = Δ.sub.k1 log D.sub.k

    Δk.sub.2 log S.sub.k = Δ.sub.k2 log D.sub.k.

On the assumption that the drift is small and that its logarithm can be regarded as varying in a parabolic manner, it is true to write

    log D.sub.k (t) = (Δ.sub.k1 log S.sub.k + Δ.sub.k2 log S.sub.k)t + 1/2Δ.sub.k12 log S.sub.k.t.sup.2,

in which Δ_(k12) signifies the second order slope derived from the first order slopes Δ_(k1) and Δ_(k2). Thus the drift D_(k) (t) is determined for all times t during the examination cycle in terms of the four signal outputs ##EQU9## and ##EQU10## Every signal output of every detector can be corrected for drift, and knowing the drift in particular for time t = -T, the relative sensitivities of the various detectors may be allowed for as indicated earlier. Therefore the image reconstruction data can be compensated for the time variations occuring in detector sensitivity.

Referring now to FIG. 4, the output signals from the integrator 232 (FIG. 2) are applied to analogue/digital converters 233 represented in FIG. 4 by a typical unit 233_(k). This receives the output from detector k which is then applied via a logging circuit 242, and other circuit elements to be explained hereinafter, to the data store 239, in which the beam data signals as initially stored require to be corrected for errors arising from detector sensitivity differences. From the store after correction the data is selected in desired order by address selector 251 (FIG. 2). The computer timing circuit or clock 236, a route selector circuit 241_(k) and the logging circuit 242 function in known manner under control of the computer programme.

To make the nature of the computer operations more clear, the relation between a corrected and uncorrected data signal held in the store 239 will be expressed as follows:

    log f(t) = log S.sub.k (t) - log A.sub.k - log D.sub.k (t).

In this expression f(t) is the true measure of absorption of radiation along the path through the body that is incident upon detector k at time t. The value in fact measured by the detector is S_(k) (t). This value in its logarithmic form is initially stored in the data store 239 and correction is performed by subtracting from the uncorrected beam data signal the corrections log A_(k) and log D_(k) (t).

From what has earlier been said it will be realised that the correction of the data signals initially stored in store 239 requires detector output signals to be noted at times specified by:

    t = -3/2T,

    t = -T,

    t = -1/2T,

    t = 0,

    t = 1/2T,

    t = 3/2T.

for simplicity the outputs of the kth detector at these times 3/2 T, -T, -1/2T, 1/2T and 3/2 T will be denoted in accordance with: ##EQU11## and the output of detectors k+1 at time t=o will be denoted as

    S'.sub.k (o) = x.sub.3k'

These particular values, which appear in the output of the analogue-to-digital converter 233_(k), are routed by the route selecting circuit 241_(k), acting under the control of the timing circuit 236, to the kth address of respective stores 250₀, 250₁, 250₂, 250₃, 250₄, 250₆ as indicated. In these stores there is an address in each case corresponding to every detector channel, of which the kth is typical. It will be realised that the values in question except for x_(3k') also constitute image reconstruction data and are also stored in the data store 239. When the signals have been in stores 250₀, 250₁, 250₂, 250₃, 250₄, 250₆ a selector circuit 251_(k) withdraws the values x_(0k') x_(2k), x_(4k) and x_(6k) in sequential manner, under control of the timing circuit 236, so as to feed them in sequence to the logging circuit 242. They emerge from the circuit 242 in logarithmic form and are applied to the differencing circuit 252_(k), which forms the first and second order slopes earlier introduced, and transfers these slope values to the drift function synthesis circuit 253_(k). This last circuit uses these values and values of the time parameter t to generate values of the logarithmic drift function log D_(k) (t), in accordance with the assumption that this function varies parabolically with t as set out earlier. The values of t used in generating values of the function are those appropriate to the time of generation of the data signals fed to the store 239. Respective values of the function log D_(k) (t) are applied to an adder circuit 254_(k) and thence subtractively to appropriate addresses in the data store 239. The appropriate values of t are communicated to the synthesis circuit 253_(k) over the conductor 245_(k). In this way the data signal held in store 239 originating from the detector k are corrected for all values of the parameter t used in image reconstruction. Following the same processing in similar circuit arrangements for all detector channels the entire data in store 239 is corrected for detector drift errors.

To follow the method of compensating the store data for position sensitive errors, that is unequal detector sensitivities it will first be noted that ##EQU12## in consequence of which, if ##EQU13## it follows that ##EQU14##

The compensation for unequal detector sensitivites involves the appropriate subtraction of the differing values of log A_(k), differing for different values of k, from the data stored in store 239. Since the value log A₁ is common to all corrections, this value is disregarded on the ground that it would only introduce a uniform component into the image reconstruction. Thus where the value of log A_(k) is referred to in future it will be understood to have the meaning ##EQU15## From the discussion of the problem that has been given earlier it will be evident that the value of log λ_(k) is given by the equation

    log x.sub.3k' - log x.sub.1k = logλ.sub.k - log D.sub.k (-T),

in which, as stated earlier

    k' = k+1.

The selector circuit 255_(k) under control by the timing circuit 236 selects in sequence the stored value x_(3k'), stored in store 250₃ and the stored value x_(1k) from the store 250₁ to apply them in turn to the logging circuit 242 and thence to a sensitivity comparison circuit 256_(k). This circuit uses the applied values together with the value of log D_(k) (-T) generated by the drift function synthesis circuit 253_(k), and fed to the circuit 256_(k) under timing control by circuit 236, to synthesise the value of logλ_(k) in accordance with the above equation giving logλ_(k). The value of logλ_(k) so synthesised is fed to the kth address of sensitivity store 257 which progressively receives and stores values of logλ_(k) for all values of k. All values of logλ_(k) are synthesised by respective circuits of the character just indicated.

To generate the value of log A_(k) the adder circuit 258_(k) withdraws from store 257 all stored values of logλν for values of ν given in the range 1, 2, 3, . . .k-, 1 under the timing control of circuit 236 via conductor 245'_(k), and sums them so generating the required value of log A_(k). This value is applied to the adder circuit 254_(k) and thence subtractively to the appropriate addresses in store 239. Using similar procedures to include all values of k the data stored at all addresses of data store 239 are compensated substantially for the unequal sensitivites of the detectors.

The components and circuits illustrated in FIG. 4 are merely shown diagrammatically because they are as already stated, implemented by a suitably programmed digital computer, which may be of any well known construction.

It will be understood that while detector values used in data signal correction as described are those of one detector position only, these values may be values averged over a group of positions. In this way statistical errors from limited photon counts can be significantly reduced.

Furthermore, the detector values used in correction need not be obtained at the times indicated provided the timing of the circuit is arranged accordingly. Shorter scans and altered timings may be employed if desired to reduce the total time of scanning.

During the second revolution of the examination cycle, signals are derived from the detectors 18 only at time t = o. During the remainder of the revolution the X-rays may be cut off to reduce patient dose. Alternatively however, data signals may be generated during this second revolution and utilised in the image reconstruction.

It will be appreciated that the correction for time variable errors in detector sensitivity is achieved by deriving output signals from the respective detector at successive times when the radiation is incident on the detector, through the body being examined, along the same beam path. These output signals are utilised to generate a function representing the form of the drift in sensitivity, and discrete values of this function evaluated for respective instants of time are used to correct the respective output signals generated at the corresponding instants. Depending on the number of output signals used to generate the drift function, the function may be linear, parabolic, cubic or even higher order. In practice however parabolic function gives adequate correction. This aspect of the invention can be utilised with any number of detectors, since an individual drift function is generated for each detector. It is applicable where only one detector is used in each plane to be investigated, as described for example in U.S. Pat. No. 3,778,614.

The position sensitve correction is however based on receiving radiation along the same path by particular pairs of detectors (which need not in practice be constituted by adjacent detectors) in a detector system, one path for each pair. This aspect of the invention is therefore applicable only where multiple detectors are used. In the example described, the desired result is achieved by directing radiation twice through the body from substantially identical directions, and sensing the radiation emerging from the body at the first time with the detectors in one position relative to the body, and the second time with the detectors in a displaced position relative to the body. It will be understood however that the same effect could be achieved by displacing the body relative to the detectors, or by a combination of such movements. Moreover, the "look" through the body with the detectors displaced from their positions they occupy for normal scanning may take place either before and after the scanning movement, instead of as described, at an intermediate point. It is however preferable to check the relative sensitives of the detectors at an intermediate point in the scanning process.

In the example described above the invention is used in a medical radiology machine of the type sometimes referred to as CAT scanners, in which radiation travels along a substantially planar slice through the patient. The X-radiation source orbits around the patient so as to tend radiation along a number of directions which are at different angles to each other but are all in the slice. The intensity of the radiation emerging from the slice is measured along each of a number of pencil-thin beam paths such that any point in the slice is traversed by a great number of such beam paths. The resulting measurements are processed, for example as described in U.S. Pat. Nos. 3,778,614 and 3,924,129, to generate a picture in which each point has a brightness corresponding to the X-radiation response characteristics of the correspondingly positioned point in the slice. The picture is similar to what would be seen if the patient were cut in two along the slice and one looked at the resulting cross-section through the body.

The detectors of the X-radiation are often operated near the limits of their capabilities in order to minimize the radiation dosage to the patient and to minimize the time for an examination. As a result even small differences among the sensitivities of the several detectors and even small drifts in the individual sensitivities of the detectors may become significant, and the picture may be degraded thereby. Accordingly, one aspect of the invention relates to carrying out an examination in such a way that the effects of differences between detector sensitivities and drift in detector sensitivity are reduced. In the example of the invention described above this desired goal is accomplished by modifying the orbiting motion such that at least two detectors look (at different times) along the same beam path, and additionally each detector detects (at different times) radiation along the same beam path. When two detectors detect radiation that has traversed the same path through the patient, any difference in the two measurements is attributed to difference between the sensitivities of the detectors. When the same detector detects radiation along the same path at different times, any difference in the two measurements is attributed to drift in the sensitivity of that detector. To correct for difference in sensitivities as between different detectors one detector may be assumed to be accurate and the measurements derived from all other detectors may be adjusted to reflect any measured differences in sensitivity with respect to that detector. To compensate for the drift of a detector during an examination two or more measurements taken by that detector for the same path at different times are fitted to an arbitrary curve, for example a parabolic curve, and each of the measurements taken with that detector during the complete examination interval or during a part of this examination interval is corrected in accordance with that curve. 

What I claim is:
 1. An apparatus for examining a body by means of penetrating radiation such as X- or γ- radiation including source means arranged to irradiate a region of the body, detector means, including a plurality of detectors, arranged to determine the intensity of the radiation after passage through the body, scanning means arranged to scan said source and detector means relative to the body to irradiate the body by the source means from a plurality of directions so that there can be derived, from said determinations of intensity, a reconstruction of the distribution of absorption of the radiation within a part of the body, means being provided to compare the outputs of said detectors in pairs at predetermined times when the respective detectors of a pair receive radiation along substantially identical paths to determine the differences in the relative sensitivities of said detectors during the scanning movement.
 2. Apparatus according to claim 1 including means for changing the relative positions of the detectors and the body as between a first and a second portion of the scanning movement to cause each detector to receive radiation during one of said portions along a path substantially identical to the path along which another detector has received radiation during the other portion of the scanning movement.
 3. Apparatus according to claim 1 wherein said scanning means includes means for causing each detector to receive radiation along substantially identical paths at different times of the scanning movement, and means are provided for compensating for drift in the sensitivity of each said detector in response to a comparison of the output derived from the respective detector at said different times.
 4. Apparatus according to claim 3, wherein said scanning means includes means for causing each detector to receive radiation along substantially identical paths a sufficient number of times for said compensation for drift to be predicted on a parabolic law of drift.
 5. Apparatus for examining a body by means of penetrating radiation such as X- or γ- radiation including source means arranged to irradiate the body, at least one detector arranged to determine the intensity of the radiation after passage through the body along a beam path, and scanning means arranged to scan said source and said detector means with respect to the body so that said body is irradiated by the source means from a plurality of positions, whereby a reconstruction of the distribution of absorption of the radiation with a part of the body can be obtained, and wherein said scanning means includes means for causing said detector means to receive radiation along substantially identical paths at different times, and means are provided for compensating for drift in the sensitivity of said detector in response to a comparison of the outputs derived from said detector at said different times.
 6. A method of examining a body by means of penetrating radiation such as X- or γ- radiation including the steps of irradiating a region of the body, detecting the intensity of the radiation, after passage through the body, scanning the source of the radiation and a plurality of detectors with respect to the body to irradiate the body by the source from a plurality of directions, and deriving from said detecting of intensity a reconstruction of the distribution of absorption of the radiation within a part of the body, said deriving step including comparing the outputs of said detectors in pairs at predetermined times in the course of the scanning to determine the extent of differences in the sensitivities of the detectors.
 7. A Radiographic apparatus for medical diagnostic examination including source means arranged to irradiate a body with penetrating X-radiation, detector means arranged to detect said radiation after it has traversed the body, means for scanning the source and detector means relative to the body so as to permit the detection of radiation traversing the body along a plurality of substantially coplanar paths, some at least of said paths being arranged to intersect one another within the body, said detector means including a plurality of detectors and said scanning means including means for causing each detector to detect radiation along substantially identical paths at different times and for causing different detectors to detect radiation along substantially identical paths at different times, means for deriving from the detectors signals indicative of the amount of the radiation detected by the detectors along said coplanar paths and indicative of drift in the sensitivity of each detector and of differences between the sensitivities of different detectors, and means for processing the last recited signals to construct a representation of the section of the body defined by the paths.
 8. A radiographic apparatus as in claim 7 wherein the scanning means include means for orbiting the source and detector means around the body through three revolutions and the means for causing each detector to detect radiation along substantially identical paths at different times and for causing different detectors to detect radiation along identical paths at different times comprise means for shifting the position of the detectors within said plane and with respect to the body by a distance corresponding to an integer multiple of the distance within said plane between detectors.
 9. A medical radiology device comprising:means defining a patient position and means disposed outside the patient position for generating a swath of penetrating radiation which is within a substantially planar region of space that intersects the patient position, said swath traveling along the region and emerging from the patient position after suffering absorption determined by the matter through which it has travelled within the region; means for orbiting the generating means around an axis transverse to the plane of the swath to cause the swath of radiation to travel within said substantially planar region along a plurality of successive directions which are at an angle to each other; means for detecting the radiation emerging from the patient position, said detecting means comprising a plurality of detection devices receiving radiation emerging from the patient position along a plurality of different substantially linear paths through the region and means for deriving from the detection devices successive sets of measurement signals, each set comprising a measurement signal for each of a plurality of different paths within the swath of radiation along one of said directions of the swath; means for causing at least one of: a) each detector to receive radiation along a substantially identical path through the patient position at different times of said orbiting; and b) different detectors to receive radiation along substantially identical paths at different times in said orbiting; means for deriving from said measurement signals signals indicative of at least one of: a) drift in the sensitivity of each detector in the course of said orbiting and b) differences between the sensitivities of different detectors in the course of said orbiting; and means for processing the measurement signals in accordance with corrections determined by at least one of said signals indicative of drift and said signals indicative of differences in sensitivity to construct a representation of the radiation absorption characteristics of the matter traversed by the radiation within said region.
 10. Medical radiographic apparatus for examining a section of a patient's body by means of X-radiation, the apparatus comprising a source for projecting a substantially planar spread of said radiation through said section, a plurality of detectors for detecting the radiation projected through said section along respective beam paths irradiated by the spread, scanning means for orbiting the source and detectors around the body about an axis intersecting said spread and passing through said section, said detectors each producing successive output signals during an orbital movement through a substantial angle, each signal relating to a respective beam path through said section, means for effecting relative movement, at least between said detectors and said body, after said orbital movement has been effected so that each detector receives radiation projected through said section along a beam path which substantially overlies a beam path in respect of which another detector produced output signals during said orbital movement, means for comparing the output signals produced by different detectors and relating to radiation projected through the section along substantially the same beam path so as to generate comparison signals indicative of the relative sensitivities of said different detectors, and processing means for modifying the output signals produced by said detectors during said orbital movement, in dependance upon said comparison signals, to allow for said relative sensitivities, and for operating upon the modified output signals to evaluate the absorption or transmission coefficient, with respect to said radiation, at each of a plurality of locations in said section.
 11. Radiographic apparatus comprising a source of penetrating radiation, such as X- or γ- radiation, means defining a patient position to be occupied by a cross-sectional slice of the body of a patient under examination, support means supporting said source so that said radiation projects across said patient position along a plurality of divergent beam paths, scanning means for causing said support means, and with it said source, to move angularly around said patient position so that said radiation projects across said patient position along further beam paths, detector means, including a plurality of detector devices, adapted to align with, and receive radiation emergent from said patient position along said beam paths and to provide output signals indicative of the absorption suffered by said radiation on traversing said beam paths, means being provided for causing relative movement between said source and said detector means, at at least one stage during the angular movement of said support means around said patient position, causing at least some of said detector devices to align with, and receive radiation emergent from said patient position along beam paths with which other detectors have also been aligned and processing means for operating on the output signals to provide a representation of the distribution of absorption in said cross-sectional slice, the processing means including means for taking an output signal, provided by a detector device for a beam of radiation projected through said region at said one stage of the angular movement, and a second output signal, provided by a different detector device for substantially the same beam of radiation projected through said region at said another stage of the angular movement, and for using both of the output signals, which are together indicative of sensitivity differences between the first and second detectors, to compensate the representation for said sensitivity differences.
 12. Apparatus according to claim 11 including processing means for processing all of the output signals, including those derived after said relative movement between said source and said detector means, to produce a representation of the variation of absorption coefficient, with respect to said radiation, over said slice of the patient's body. Apparatus according to claim 11 wherein said relative movement between said source and said detector means comprises an angular movement of said detector means relative to said source as axis.
 14. Apparatus according to claim 13 wherein said detector devices are also supported by said support means and move therewith angularly around the patient position.
 15. Apparatus according to claim 14 wherein said means for causing relative movement between said source and said detector means comprises means for moving said detector means relative to said support means.
 16. Apparatus according to claim 13 wherein said radiation subtends an angle, at said source, which exceeds the angle subtended at said source by said detector means by an amount sufficient to accommodate said relative movement between said source and said detector means. 